Methods and systems for enhanced fluid transport

ABSTRACT

The present invention generally provides methods for enhancing transport and direction of materials in fluidic systems, which systems utilize electroosmotic (E/O) flow systems, to affect that transport and direction. The methods generally comprise providing an effective concentration of at least one zwitterionic compound in the fluid containing the material that is to be transported or directed.

CROSS REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. patent application Ser. No.09/309,365, filed May 11, 1991 now U.S. Pat. No. 6,129,826, which is acontinuation of U.S. patent application Ser. No. 08/833,279, filed Apr.4, 1997, now U.S. Pat. No. 5,964,995, the full disclosures of which areincorporated herein by reference.

BACKGROUND OF THE INVENTION

There has been a growing interest in the development and manufacturingof microscale fluid systems for the acquisition of chemical andbiochemical information, in both preparative and analytical capacities.Adaptation of technologies from the electronics industry, such asphotolithography, wet chemical etching and the like, has helped to fuelthis growing interest.

One of the first areas in which microscale fluid systems have been usedfor chemical or biochemical analysis was in the area of capillaryelectrophoresis (CE). CE systems generally employ fused silicacapillaries, or more recently, etched channels in planar silicasubstrates, filled with an appropriate separation matrix or medium. Asample fluid that is to be analyzed is injected at one end of thecapillary or channel. Application of a voltage across the capillary thenpermits the electrophoretic migration of the species within the sample.Differential electrophoretic mobilities of the constituent elements of asample fluid, e.g., due to their differential net charge or size,permits their separation, identification and analysis. In order tooptimize the separation aspect of the CE applications, researchers havesought to maximize the electrophoretic mobility of charged speciesrelative to each other and relative to the flow of the fluid through thecapillary resulting from, e.g., electroosmosis. See, e.g., U.S. Pat. No.5,015,350, to Wiktorowicz, and U.S. Pat. No. 5,192,405 to Petersen etal.

In comparison to these CE applications, the technologies of theelectronics industry have also been focused on the production of smallscale fluidic systems for the transportation of small volumes of fluidsover relatively small areas, to perform one or more preparative oranalytical manipulations on that fluid. These non-CE fluidic systemsdiffer from the. CE systems in that their goal is not theelectrophoretic separation of constituents of a sample or fluid, but isinstead directed to the bulk transport of fluids and the materialscontained in those fluids. Typically, these non-CE fluidic systems haverelied upon mechanical fluid direction and transport systems, e.g.,miniature pumps and valves, to affect material transport from onelocation to another. See, e.g., Published PCT Application No. 97/02357.Such mechanical systems, however, can be extremely difficult andexpensive to produce, and still fail to provide accurate fluidic controlover volumes that are substantially below the microliter range.

Electroosmotic (E/O) flow systems have been described which provide asubstantial improvement over these mechanical systems, see, e.g.,Published PCT Application No. WO 96/04547 to Ramsey et al. Typically,such systems function by applying a voltage across a fluid filledchannel, the surface or walls of which have charged or ionizeablefunctional groups associated therewith, to produce electroosmotic flowof that fluid in the direction of the current. Despite the substantialimprovements offered by these electroosmotic fluid direction systems,there remains ample room for improvement in the application of thesetechnologies. The present invention meets these and other needs.

SUMMARY OF THE INVENTION

The present invention generally provides methods, systems and deviceswhich provide for enhanced transportation and direction of materialsusing electroosmotic flow of a fluid containing those materials. Forexample, in a first aspect, the present invention provides methods ofenhancing material direction and transport by electroosmotic flow of afluid containing that material, which method comprises providing aneffective concentration of at least one zwitterionic compound in thefluid containing the material.

In a related aspect, the present invention also provides methods ofreducing electrophoretic separation of differentially charged species ina microscale fluid column, where that fluid column has a voltage appliedacross it, which method comprises providing an effective concentrationof at least one zwitterionic compound in the fluid.

The present invention also provides microfluidic systems whichincorporate these enhanced fluid direction and transport methods, i.e.,provide for such enhanced fluid transport and direction within amicroscale fluid channel structure. In particular, these microfluidicsystems typically include at least three ports disposed at the terminiof at least two intersecting fluid channels capable of supportingelectroosmotic flow. Typically, at least one of the intersectingchannels has at least one cross-sectional dimension of from about 0.1 μmto about 500 μm. Each of the ports may include an electrode placed inelectrical contact with it, and the system also includes a fluiddisposed in the channels, whereby the fluid is in electrical contactwith those electrodes, and wherein the fluid comprises an effectiveconcentration of a zwitterionic compound.

BRIEF DESCRIPTION OF THE FIGURES

FIGS. 1A to 1C are schematic illustrations of the effects ofelectrophoretic mobility of charged species on the migration of thosespecies in a coherent electroosmotic fluid flow. FIG. 1A illustrates anoptimal scenario where differentially charged chemical species containedin discrete fluid volumes have apparent mobilities that aresubstantially the same as the electroosmotic flow rate for the fluid.FIG. 1B illustrates the situation wherein the apparent mobility ofpositively charged species is greater than the rate of electroosmoticflow and the apparent mobility of negatively charged species is lessthan or opposite to the rate of electroosmotic flow, resulting in theelectrophoretic biasing of the charged species within the discrete fluidvolumes. FIG. 1C illustrates the situation where the apparent mobilitiesof charged species are substantially different from the rate ofelectroosmotic flow of the fluid, such that the charged species in thetwo discrete fluid volumes overlap.

FIG. 2 is a graph showing the effect of the addition of sulfobetaine onelectroosmotic flow and apparent mobility of charged species, underconditions of electroosmotic flow.

FIG. 3 illustrates a microfluidic device used to perform enzymeinhibitor assays.

FIG. 4 illustrates a graphical comparison of enzyme inhibition assays inthe presence and absence of a zwitterionic compound, NDSB.

DETAILED DESCRIPTION OF THE INVENTION

I. General

The present invention generally provides methods and systems for theenhanced transportation and direction of materials within fluidicsystems, which utilizes the electroosmotic flow of fluids containingthose materials. By “enhanced transportation and direction” is generallymeant the electroosmotic flow and direction of fluids within fluidicsystems, which shows: (1) a reduction in the electrophoretic mobility ofa charged species relative to the electroosmotic flow of the fluidcontaining that charged species; and/or (2) an increase in the overallelectroosmotic flow of that fluid, relative to such systems notincorporating the present invention, as described herein.

A. Reduction of Electrophoretic Mobility of Charged Species

As noted previously, in capillary electrophoresis applications, thegeneral goal is to maximize the separation between different speciescontained in a sample of interest, in order to separately analyze thosespecies, identify their presence within the sample, or the like. This isaccomplished by maximizing the differences in the electrophoreticmobilities of these species, which differences may result fromdifferences in their size and/or net charge.

In the E/O fluid direction systems described herein, however, the goalsare somewhat different from those of CE systems. In particular, thegeneral object of these E/O fluid direction systems is the transportand/or direction of material of interest contained in a volume of fluidor multiple discrete volumes of fluid, from one location in the systemto another, using controlled E/O flow. Because these fluids aregenerally to be subjected to further manipulation or combination withother fluids, it is generally; desirable to affect the transportation ofthese fluids without substantially altering their make-up, i.e.,electrophoretically separating or biasing differentially charged orsized materials contained within those fluids.

Similarly, where these systems are being used to serially transportsmall volumes of fluids or multiple discrete volumes of different fluidsalong the same channels, it is generally desirable to transport thesefluid volumes as coherently as possible, i.e., minimizing smearing ofmaterials or diffusion of fluids. In particular, because these systemsare preferably utilized in microfluidic applications, the improvedcoherency of a particular fluid volume within the E/O flow systempermits the transport of larger numbers of different fluid volumes perunit time. Specifically, maintaining higher fluid volume coherencyallows separate volumes to be transported closer together through thechannels of the system, without resulting in excessive intermixing ofthese volumes. Further, maintenance of maximum fluid volume coherencyduring the transport and direction of the fluids permits more precisecontrol of volumetric delivery of materials within these systems.

Despite the differing goals of the CE systems and the E/O flow systemsused in the present invention, in each case, the application of anelectrical field across a fluid of interest has the same basic result.Specifically, where the fluid of interest comprises charged species, oris made up of a plurality of differentially charged chemical species,application of a voltage across that fluid, e.g., to obtain E/O flow,will result in those charged species electrophoresing within the fluid,and the differentially charged species electrophoresing at differentrates. As such, in a channel having a negative surface potential,negatively charged species will have an electrophoretic mobilityopposite to the direction of E/O flow, whereas positively chargedspecies will have an electrophoretic mobility in the same direction ofE/O flow. The greater the number of charges a particular species has,the greater its electrophoretic mobility in the same or oppositedirection of E/O flow. In systems employing electroosmotic fluiddirection, this results in a net separation of differentially chargedspecies that are contained within the fluid that is being transported.

Where one is transporting a particular volume of a given sample fluid,this separation can result in an electrophoretic biasing of the sample,where the positively charged species have a greater apparent mobility,than negatively charged species. “Apparent mobility” as used herein,generally refers to the overall mobility of a given species within thefluidic system. In the systems of the present invention, apparentmobility is typically-defined as the rate of E/O mobility plus theelectrophoretic mobility. Where electrophoretic mobility is opposite tothe direction of E/O flow, i.e., negative, this leads to an apparentmobility that is less than the E/O mobility.

In the case of species having high electrophoretic mobility,.e.g.,highly charged species, the effect can be magnified to the point thatthe apparent mobility of such species is substantially different fromthe E/O mobility of the fluid containing them. For example, speciespossessing multiple negative charges may have an electrophoreticmobility substantially opposite the direction of E/O mobility, resultingin a substantial-reduction in the apparent mobility of that species.Where that reduction is sufficiently large, it can result in thatspecies being effectively “left behind” by the particular volume offluid that is being transported.

Conversely, a species bearing multiple positive charges may have anapparent mobility that is far greater than that of the fluid beingtransported and other species contained therein, such that the speciesis transported well ahead of the fluid volume.

This problem is not as significant where one is transporting largevolumes of fluid from one location to another. Specifically, one canreduce the effects of the electrophoretic separation of a fluid bycollecting larger volumes, thereby reducing the contribution that biasedportions of the fluid have on the overall fluid delivered.

However, the problem is substantially magnified when one wishes totransport a relatively small volume, or multiple small volumes of thesame or different fluids, without separating the materials contained inthe individual fluid volumes or intermixing the materials contained inseparate volumes. Specifically, in transporting a one or a series ofdiscrete volumes of a particular fluid or fluids, e.g., samples, testcompounds, various elements of a screening system, species that haveapparent mobilities that are substantially different from the E/Omobility of the particular fluid volume will travel ahead of, and behindthe fluid volume, effectively smearing the materials that are sought tobe delivered. As described above, this is a significant disadvantagewhere relatively precise fluid control is desired, or where smallereffective volumes are used. For example, where one is screening forcompounds which affect a particular reaction mix, e.g., a biochemicalsystem, it is generally desirable to be able to mix the elementsnecessary for that screen, e.g., enzyme, substrate and test inhibitor,and allow those elements to incubate together while transporting them tothe ultimate detection area. Where those elements separate based upontheir differential electrophoretic mobilities, this can have substantialadverse effects on the overall efficacy of the screening system.

More importantly, where a species in a first volume being transportedhas an apparent mobility that is substantially less than the E/Omobility of the fluid, while a species in a second or following volumehas an apparent mobility that is substantially greater than the E/Omobility of the fluid that is being delivered, those two species canoverlap within the flow system.

The above described problems are schematically illustrated in FIG. 1.FIG. 1A shows an optimal situation where discrete volumes or regions offluids in a channel (fluids AB and XY, shown underlined) containdifferentially charged species, e.g., X+ and Y−, and A+ and B−. In thisoptimal situation, these differentially charged chemical species have anapparent mobility that is not substantially different from the E/Omobility of the fluid containing those species. As a result, the variousspecies are maintained substantially within their separate fluidregions. FIG. 1B illustrates the smearing effect which results whencharged species, as a result of their greater electrophoreticmobilities, begin to migrate outside of their respective fluid volumesor regions. This results in a smearing of the materials that are beingtransported and substantially reduces the precision with which thesematerials can be transported. Finally, FIG. 1C illustrates the situationwhere the apparent mobility of the charged species is so substantiallydifferent from the E/O mobility of the fluid regions, that it results inthe overlapping and intermixing of differentially charged species fromdifferent fluid regions. The intermixing of separate fluid volumescreates substantial problems where the fluid system is being used in theserial transport of multiple different fluids, e.g., as described inU.S. Pat. No. 6,046,056, and incorporated herein by reference in itsentirety for all purposes.

Methods have been developed to prevent and/or correct for the excessiveelectrophoretic mobility of charged species, when those species arebeing transported in E/O fluid direction systems, by incorporating fluidbarriers around the fluid being transported, in which theelectrophoretic mobility of these charged species is substantiallyreduced, see, e.g., commonly assigned U.S. Pat. No. 5,880,071incorporated herein by reference in its entirety for all purposes.

Generally, the enhanced E/O material transport and direction produced bythe present invention is carried out by providing within the fluidcomponent of the system, a compound or compounds that are capable ofreducing the effects such an E/O system has on charged species containedwithin the fluid. For example, incorporation of these compounds withinthe fluid component of the E/O flow system typically results in areduction in the electrophoretic mobility of charged species, and thus,reduces the differential electrophoretic mobility and apparent mobilityof differentially charged species.

In preferred aspects, zwitterionic compounds or combinations thereof,are used to reduce the electrophoretic mobility of materials that arecontained within the fluids that are sought to be transported usingthese E/O fluid direction systems, thereby achieving or substantiallyachieving the optimal situation shown in FIG. 1A.

Without being bound to a particular theory of operation, it is believedthat such zwitterionic compounds interact with the charged species in alayer-like complex. The “complex” has the same net charge as the chargedspecies, but that charge is spread over a much larger structureeffectively reducing the charge:size ratio, and reducing theelectrophoretic mobility of the complex. Because zwitterions are dipolarmolecules, they can be effectively employed with respect to positivelyor negatively charged species.

While other methods can be used to effectively reduce the charge:sizeratio of compounds in an E/O fluid direction system, these methods havenumerous associated problems. For example, raising or lowering pH of thefluid containing the species can effectively reduce the level of chargeof a chemical species by protonating or deprotonating functional groupspresent therein. While effective in reducing net charge of a givenspecies, this method can have substantial adverse effects. Specifically,where the fluidic system is being utilized in the analysis of biologicalsystems, e.g., enzymatic reactions, receptor/ligand interactions, or intransporting other materials sensitive to extremes of pH, thesubstantial variation of pH, e.g., from neutral or physiologicalconditions, can place the system well outside the optimal pH forsubsequent manipulation or analysis. In some cases, the optimal pH forreducing the net charge of a particular species may denature orotherwise degrade active components of the materials that are beingtransported.

The incorporation of zwitterionic compounds as described herein, on theother hand, is readily compatible with systems to be used for thetransport of pH sensitive materials, e.g., systems used in analysis ofbiological systems. In particular, different zwitterionic compounds,i.e., having different pI, may be selected depending upon the pHsensitivity of the material being transported. Accordingly, as can bereadily appreciated from the foregoing, the present invention isparticularly useful in E/O fluid direction systems where the materialsto be transported include biological material, such as enzymes,substrates, ligands, receptors, or other elements of biological orbiochemical systems, e.g., as those systems are defined in U.S. Pat. No.6,046,056, previously incorporated herein by reference for all purposes.

Another method that can be used to affect the charge:size ratio of acharged molecule of interest in an E/O fluid direction system involvesinteracting that charged molecule of interest with another molecule orspecies such that the two molecules form a complex having a differentcharge:size ratio. Merely by way of example, fluorescein is a moleculethat carries two negative charges above neutral pH. The electrophoreticmobility of this molecule can be readily altered by adding an antibody,such as anti-fluorescein to the solution. The resulting complex willhave a substantially reduced electrophoretic mobility over that offluorescein alone. Again, while this method is effective, it too carriesa number of disadvantages. First, because one must identify a compoundthat associates with the charged molecule of interest, a specificallyassociating compound must be identified for each charged molecularspecies in the fluid, and for each different fluid used in the system.Further, as is the case with the fluorescein/anti-fluorescein complexdescribed above, incorporation of an active molecule into a largercomplex can have an adverse effect on the desired activity or functionof that molecule, i.e., substantially reduced fluorescence.

The methods and systems of the present invention, on the other hand donot have these associated problems. For example, the function ofzwitterionic compounds in reducing electrophoretic mobility of chargedspecies is generally applicable, i.e., does not require a specificinteraction between the charged species and the zwitterion. Further, thenature of this interaction results in little or no effect on theproperties of the charged molecule of interest.

B. Increase In E/O Mobility

In addition to the advantages of reducing the electrophoretic mobilityof charged species within fluids that are being transported using E/Ofluid directions systems, incorporation of zwitterionic compounds inmany systems can also have the effect of increasing the E/O mobility inthe fluid direction system, thereby further optimizing the apparentmobility of the material that is being transported.

In particular, incorporation of zwitterionic compounds within fluidsbeing transported in E/O fluid direction systems has been shown toincrease E/O mobility of those fluids. This effect is particularlyapparent where those fluids include a protein component or other largercharged molecular species.

II. Compounds Useful in Practicing the Invention

A wide variety of zwitterionic and related chemical compounds may beemployed according to the present invention. For example, such compoundsinclude, e.g., betaine, sulfobetaine, taurine, aminomethane sulfonicacid, zwitterionic amino acids, such as glycine, alanine, β-alanine,etc., and other zwitterionic compounds such as HEPES, MES, CAPS, tricineand the like. In particularly preferred aspects, non-detergent, lowmolecular weight sulfobetaines are used in the methods of the presentinvention, such as dimethylethylaminopropane sulfonic acid,dimethylbenzylaminopropane sulfonic acid, and 3-(N-pyridinium)propanesulfonic acid.

Although generally described in terms of single species of zwitterioniccompounds, it will be readily appreciated that the present inventionalso comprehends the use of combinations of the above describedcompounds. Such combinations can be readily tailored to optimize theeffects seen on the overall fluidic system, as well as for theircompatibility with the various components of the system, e.g., buffers,enzymes, substrates, receptors, ligands, test compounds, and the like.

Generally, the concentration of zwitterionic compounds within the fluidscontained in the system, may be varied depending upon the effectdesired, where lower concentrations yield less of an effect in reducingelectrophoretic mobilities of materials contained within the fluid.Further, these effects may also be varied depending upon the nature ofthe charged species contained within the material of interest.Therefore, as used herein, the term “effective concentration” refers toa concentration of zwitterionic compounds that is sufficient to achievea desired effect, and particularly, achieve some reduction in theelectrophoretic mobility of a charged species of interest. Further, by“concentration” of zwitterionic compounds in the fluid” is meant theamount of such compounds added per unit volume, regardless of anysubsequent conversion of such compounds within the fluid system.Typically, however, effective concentrations of zwitterionic compoundswill preferably be greater than about 5 mM, typically greater than about10 mM, and often greater than about 50 mM. Although zwitterioniccompounds may generally be present at levels approaching theirsolubility limits in practicing the present invention, preferredconcentrations of the zwitterionic compounds in the fluid that is soughtto be transported within the system will range between about 1 mM and 2M and more preferably between about 5 mM and 2 M.

III. Application to Microfluidic Systems

As noted previously, the present invention finds particular utility influidic systems that employ E/O fluid direction systems, and moreparticularly, microscale fluidic systems. By “E/O fluid directionsystems” is generally meant fluidic systems that are made up of fluidchannels or passages, chambers, ports or the like, wherein the movementof fluid within the systems, i.e., through the channels, or from onechannel to another channel, or from one chamber to another chamber, isselectively directed through the controlled electroosmotic flow of thatfluid. Examples of such controlled E/O flow systems are described in,e.g., Published PCT Application No. WO 96/04547, and commonly owned U.S.Pat. Nos. 6,046,056 and 5,880,071, each of which was previouslyincorporated herein by reference.

In preferred aspects, such fluid direction systems direct a fluid ofinterest through intersecting channel structures by applying a voltagegradient along the desired path of fluid flow. Voltages are typicallysimultaneously applied along the intersecting fluid paths, in order topropagate a containing or directing fluid flow, i.e., to contain ordirect the fluid of interest along the desired path. For example, wherethe fluid of interest is being flowed along a first channel that isintersected by second channel, the flow of the fluid of interest ismaintained within the first channel, i.e., prevented from diffusing intothe intersecting channel, by simultaneously flowing fluid into the firstchannel from each side of the intersecting channel. This is generallydone by simultaneously applying a voltage from the originating end tothe terminating end of the first channel, and to each end of theintersecting channel, whereby appropriate E/O flow is obtained. As canbe appreciated, this results in a fluid flow pattern in the firstchannel that appears “pinched.” In another example, a fluid of interestmay be directed from a first arm of a first channel into a first arm ofan intersecting channel, by applying a voltage across the desired fluidflow path to generate fluid flow in that direction. In order to controlfluid flow at the intersection, a containing fluid flow is generatedalong the entire length of the intersecting channel creating what istermed a “gated” flow. The fluid of interest can then be metered out ordispensed in a controlled fashion, into the remaining arm of the firstchannel by actively modulating the voltage to allow the fluid to flowinto that arm, while preventing diffusion. Effectively, this results ina valving system without the necessity of mechanical elements. Finally,by modulating the rate of flow of the fluid of interest through anintersection as compared to the flow of diluents flowing in from theintersecting channels, these systems can be used as diluters.

By “microscale fluidic systems” is typically meant fluid systems thatcomprise reservoirs, conduits or channels, and/or chambers, wherein atleast one cross sectional dimension, e.g., depth, width or diameter, ofa particular fluid channel and/or chamber is in the range of from about1 μm to about 500 μm, inclusive. Such microscale fluidic systems rangefrom simple capillary systems, e.g., that employ a single fused silicacapillary for delivering a particular fluid or fluids from a reservoirat one end of the capillary to the other end of the capillary, foranalysis, combination with other reagents, and the like, to more complexintegrated multichannel microfluidic devices fabricated in solidsubstrates, such as those described in U.S. Pat. No. 6,046,056,previously incorporated herein by reference in its entirety for allpurposes. In preferred aspects, the microscale fluidic system willemploy at least one channel, and more preferably at least twointersecting channels which have at least one cross sectional dimensionin the range from 1 μm to about 500 μm, and more preferably betweenabout 1 μm and 100 μm.

The combination of these microscale dimensions with the relativelyprecise fluid control, described above, permits the controlled,repeatable direction or dispensing of extremely small volumes of fluid,which volumes are dictated by the volumes of the channels and/orintersections, e.g., a sample plug at an intersection, or by the timingof fluid flow, e.g., the amount of time or length of a fluid pluginjected into a channel using gated flow.

Typically, the microfluidic systems employed in practicing the presentinvention will comprise a solid substrate that has the channels and/orchambers of the microfluidic system disposed within it. Substrates maybe prepared from a number of different materials. For example,techniques employed in the fabrication of small scale fluidic devicesare often derived from the electronics industry. As a result, substratematerials are often selected for compatibility with these manufacturingtechniques, such as silica, silicon, gallium arsenide and the like.Typically, however, semiconducting materials are not preferred forpracticing the present invention, as they are not compatible with theapplication of electric fields through fluids, without somemodification, e.g., application of an insulating layer. Accordingly, inone preferred aspect, silica substrates are preferred in practicing thepresent invention.

Other substrate materials may also be employed in the microfluidicsystems of the invention, and may generally be selected for theircompatibility with the conditions to which they will be exposed, both inmanufacturing, e.g., compatibility with known manufacturing techniques,and operation, e.g., compatibility with full range of operatingconditions, including wide ranges of salt, pH, compositions, andapplication of electric fields. Examples of such substrates includepolymeric materials, with the provision that such materials, either ontheir own, or through modification of the surfaces that contact thefluids of the system are capable of propagating E/O flow.

Typically, the substrate will have a first surface, and will begenerally planar in shape. The intersecting channels are typicallyfabricated into the surface of the substrate as grooves. As notedpreviously, the channels may be fabricated into the surface of thesubstrate using, e.g., photolithography, wet chemical etching, and otherknown microfabrication techniques. Generally, a cover layer is overlaidon the surface of the substrate to seal the grooves, forming fluidchannels or passages.

The devices generally include a number of ports or reservoirs fabricatedtherein, which ports are in electrical contact, and typically in fluidcommunication, with the intersecting channels. These ports generallyprovide a point at which electrodes can be placed in contact with thefluids, for directing fluid flow. These ports also often provide areservoir of fluids that are used in the device or system. As such, thedifferent ports are typically placed in contact with the fluid channelson different sides of a given intersection of two channels. For ease offabrication, such ports are typically placed in electrical contact witheach of the free termini of the various channels fabricated into thedevice. By “free termini” or “free terminus” is meant a nonintersectedterminus of a channel.

For ease of discussion, the microfluidic devices and systems aregenerally described in terms of two intersecting channels. However, itwill be readily appreciated that such devices and systems may readilyincorporate more complex channel structures of three, four, five, ten,twenty and more intersecting channels. Further, such devices and systemsalso include parallel channel structures where more than one mainchannel may be intersected by large numbers of cross channels.

As described above, the present invention generally relates to methodsof enhancing electroosmotic flow, and particularly, application of thesemethods to microfluidic systems which utilize such E/O flow in thetransport and direction of fluids within these systems. This is incontrast to capillary electrophoresis systems (CE) which seek tominimize E/O mobility of fluids, while maximizing differentialelectrophoretic mobility of species contained in these fluids. Oftenthis is done by incorporating a separation matrix within the channels ofthe CE systems, which furthers these goals. Thus, the presentlydescribed systems are generally described in terms of channels whichpermit or are capable of free electroosmotic flow. By this is meant thatthe channels in which E/O flow is desired will generally have asufficient surface potential for propagating E/O flow or mobility offluids and materials in those channels. At the same time these channelsare devoid of obstructions which might impede that flow, andparticularly such channels will be free of any separation media ormatrices.

The present invention is further illustrated with reference to thefollowing non-limiting examples.

EXAMPLES

The efficacy of incorporating zwitterionic compounds for reducingelectrophoretic mobility of charged species in E/O flow systems wasdemonstrated in a fused silica capillary, having 57 cm total length, 50cm effective length and internal diameter of 75 μm. All samples were runin 50 mM HEPES buffer at pH 7.5. All of the running buffers wereprepared fresh from concentrated stock solution. For each run, thesamples were pressure injected into the capillary for 20 seconds,separated at 30 kV, and detected at 254 nm. Following each run, thecapillary was rinsed with 1N NaOH for 2 minutes followed by a 5 minuterinse with replacement buffer.

The level of electroosmotic flow within the capillary was determined byincorporation of mesityl oxide (4 μl in 4 ml H₂O), a neutral detectablemarker, while effects on electrophoretic mobility were determined byincorporation of 5.0 mM dFMUP (6,8-difluoro-4-methylumbelliferylphosphate) in water, a detectable compound having two negative chargesat neutral pH.

Example 1 Use of NDSB-195

The first experiment tested the effect of the zwitterionic compound3-(N-ethyl-N,N-dimethylammonium) propanesulfonate) (NDSB-195) onelectrophoretic mobility of charged species (dFMUP) within a bufferfilled capillary, as well as on overall electroosmotic flow of thatbuffer within the capillary. The experiment was duplicated in thepresence and absence of a protein component (0.1 mg/ml BSA).

Three different concentrations of NDSB-195 were tested: 0.1 M; 0.5 M; or1.0 M final concentration, and compared to a negative control (noNDSB-195). For each run, the retention time of mesityl oxide and dFMUPwas determined, and used to calculate the E/O mobility for the run(μEO), electrophoretic mobility (μEP) of the dFMUP, and the apparentmobility (μApp) of the dFMUP (μApp=μEO+μEP). The results are shown inTable 1, below, as averages of triplicate runs:

TABLE I μEO μEO μApp μApp μEP μEP [NDSB] ×10⁻⁴ ×10⁻⁴ ×10⁻⁴ ×10⁻⁴ ×10⁻⁴×10⁻⁴ M (+BSA) (−BSA) (+BSA) (−BSA) (+BSA) (−BSA) 0 2.94 4.77 0.20 2.02−2.74 −2.75 0.10 4.31 5.42 1.54 2.87 −2.78 −2.55 0.50 5.74 5.59 3.493.34 −2.24 −2.24 1.00 5.68 5.20 3.60 3.28 −2.08 −1.92

FIG. 2 shows a plot of E/O flow, electrophoretic mobility and apparentmobility of dFMUP, as a function of increasing concentration ofNDSB-195, both in the presence and absence of BSA. The standarddeviation is also shown for each point plotted. As is apparent fromthese data, inclusion of NDSB-195 substantially reduces the netelectrophoretic mobility of dFMUP, both in the absence and presence of aprotein component (BSA). In addition to reducing this electrophoreticmobility, the incorporation of NDSB also increases the E/O flow rate ofthe system. The net result is that the apparent mobility of the chargedspecies is brought closer to the E/O flow rate of the system.

Example 2 Use of β-Alanine

A similar experiment was performed utilizing an amino acid, β-alanine,as the zwitterionic component. In particular, β-alanine was incorporatedin the same system as described above, at two different concentrations,0.50 M and 1.0 M, and compared to a negative control (containing noβ-alanine), and in the presence and absence of a protein component. pHwas not adjusted following addition of β-alanine. The results of thisexperiment are shown in Table II, below:

TABLE II μEO × μApp. × μEP × Buffer Analyte R.T. 10⁻⁴ 10⁻⁴ 10⁻⁴ 50 mMHEPES, Mes. Ox. 3.41 4.64 4.64 pH 7.5 dFMUP 8.61 1.84 −2.80 50 mM HEPES,Mes. Ox. 3.90 4.06 4.06 pH 7.5/BSA (0.1 mg/ml) dFMUP 14.82 1.07 −2.99 50mM HEPES, Mes. Ox. 3.00 5.28 5.28 pH 7.5/BSA (0.1 mg/ml)/ dFMUP 5.442.91 −2.37 500 mM ala. 50 mM HEPES, Mes. Ox. 3.00 5.28 5.28 pH 7.5/500mM ala. dFMUP 5.51 2.87 −2.40 50 mM HEPES, Mes. Ox. 2.94 5.39 5.39 pH7.5/BSA (0.1 mg/ml)/ dFMUP 4.94 3.21 −2.18 500 mM ala. 50 mM HEPES, Mes.Ox. 2.96 5.35 5.35 pH 7.5/500 mM alanine dFMUP 4.99 3.17 −2.18 R.T. =retention time (mins)

Again, incorporation of β-alanine results in a decrease in theelectrophoretic mobility of the dFMUP, and a net increase in itsapparent mobility.

Example 3 Concurrent Application to Differentially Charged Species

Each of the above examples illustrates that the incorporation ofzwitterionic compounds results in a reduction of the electrophoreticmobility of negatively charged species in the system (dFMUP). Thefollowing experiment illustrates the same efficacy in samples containingboth positively and negatively charged chemical species.

This experiment tested the effect of 1 M NDSB on the electrophoreticmobility of a positively charged species (benzylamine) and a negativelycharged species (benzoic acid) in the same capillary system describedabove. This experiment utilized two different buffer systems: 200 mMborate at pH 8.7; and 200 mM HEPES at pH 7.0. These experiments alsoincorporated dimethylformamide (DMF) as a neutral marker compound, forascertaining E/O mobility.

Table 3, below, illustrates the effect of incorporation of thezwitterionic compound NDSB on the electrophoretic mobility and apparentmobility of both positively and negatively charged species.

TABLE III μEO × μAPP × μEP × Buffer Analyte R.T. 10⁻⁴ 10⁻⁴  ⁻⁴ 200 mMBorate DMF 3.05 5.19 5.19 — pH 8.7 Benzylamine 2.04 — 7.76   2.57Benzoic Acid 7.13 — 2.22 −2.97 200 mM Borate DMF 3.26 4.86 4.86 — pH8.9, 1M NDSB Benzylamine 2.47 — 6.41   1.55 Benzoic Acid 5.43 — 2.92−1.94 200 mM HEPES DMF 2.97 5.33 5.33 — pH 7.0 Benzylamine 1.93 — 8.20  2.87 Benzoic Acid 5.25 — 3.02 −2.32 200 mM HEPES DMF 3.56 4.45 4.45 —pH 7.0, 1M NDSB Benzylamine 2.40 — 6.60   2.15 Benzoic Acid 5.84 — 2.71−1.74

From these data, it is clear that incorporation of the zwitterioniccompound NDSB in either buffer system reduced the electrophoreticmobility of both the positively charged species, benzylamine, and thenegatively charged species, benzoic acid. Further, although in thissystem, NDSB resulted in a decrease in the E/O flow rate, there wasnonetheless, a reduction in the difference between the E/O mobility andthe apparent mobility for both of the differentially charged species,e.g., the apparent mobility of the positively charged species wasreduced while the apparent mobility of the negatively charged speciesincreased.

Example 4 Enzyme Inhibition in Presence and Absence of NDSB inMicrofluidic System

An enzyme inhibition assay was performed using a microfluidic devicehaving a well/channel structure as shown in FIG. 3. Standardsemiconductor photolithographic techniques were used to etch channels 70μm wide and 10 μm deep, in a 525 μm thick soda lime glass substrate, anda second 2 mm thick layer of glass having 3 mm diameter holes drilledthrough it, was thermally bonded to the first, providing the variouswells.

All reagents were diluted in the same buffer solution which also servedas the running buffer: 25 mM HEPES, pH 7.9, for the control; and 25 mMHEPES, 1 M NDSB-195 (non-detergent sulfobetaine, MW 195)(available fromCalbiochem-Novabiochem, La Jolla, Calif.), pH 7.9, for the test run. Theassay solutions were prepared from stock solutions of 5000.U/mgleukocyte antigen related phosphatase. (LAR) (enzyme)(New EnglandBiolabs, Beverly, Mass.), 10 mM dFMUP in water, a fluorogenic substratefor LAR (substrate)(available from Molecular Probes, Eugene, Oreg.), and1.4 mM of a known competitive inhibitor of LAR (inhibitor).

Detection of fluorescence was carried out using a Nikon invertedMicroscope Diaphot 200, with a Nikon P101 photometer controller, forepifluorescent detection. An Opti-Quip 1200-1500 50 W tungsten/halogenlamp coupled through a 10× microscope objective provided the lightsource. Excitation and emission wavelengths were selected with a DAPIfilter cube (Chroma, Brattleboro, Vt.) fitted with a DM400 dichroicmirror, 340-380 nm excitation filter and 435-485 nm barrier filter.Reagent well currents and voltages on the chip were controlled using aCaliper 3180 Chip Controller (Palo Alto, Calif.). The currents andvoltages ranged +/−10 μA and 0-2000 V. Data was collected on a MacintoshPower PC 7200/120.

The channels of the device were filled with running buffer by placingthe buffer in a buffer well and allowing capillary action to distributethe buffer throughout the channels. 125 nM LAR enzyme was placed in theenzyme well, 50 μM dFMUP was placed in the substrate well and 200 μM ofa known competitive inhibitor of LAR was placed in the inhibitor well.

The assay was performed using the following injection cycle, with theindicated final reagent concentrations in the injection channel: (1)buffer; (2) substrate (17 μM); (3) buffer; (4) substrate+enzyme (83 nM);(5) buffer; and (6) substrate+inhibitor (66 μM)+enzyme. The total fluxof reagents remained constant during each step of the assay bymaintaining a constant overall sum of combined currents from the wells.

The raw fluorescent data from this experiment are shown in FIG. 4. Thecontrol data, e.g., in the absence of NDSB-195, is shown as a solidline, running at or near the baseline of the data. As can be seen fromthis data, LAR action on the dFMUP substrate produces only a moderatesignal, ranging between a fluorescent intensity of 2200 and 2250.Further, while some effect of the inhibitor is apparent through thisassay at later time points, that effect is relatively small. Withoutbeing bound to a particular theory, it is believed that this is theresult of two phenomena: (1) the LAR enzyme is interacting with thechannel walls, resulting in a smearing of the enzyme throughout theassay, as indicated by the appearance of signal in the substrate onlycontrol; and (2) the high electrophoretic mobility of the dFMUPsubstrate opposite the electroosmotic mobility of the system results inthe substrate and enzyme being separated, thereby reducing the abilityof the enzyme to act on the substrate.

Upon inclusion of NDSB-195 in the assay system, however, the data becamemuch clearer (dashed line). In particular, the inclusion of NDSB in thisassay shows dramatic improvements in signal over the same system withoutthe zwitterionic component, including a lack of signal in the substrateonly control. Further, the effects of the inhibitor also are much moredramatic and clearly evident. The assay was run in continual cycle forsix hours with no detectable loss of signal or increase in backgroundfluorescence.

All publications and patent applications are herein incorporated byreference to the same extent as if each individual publication or patentapplication was specifically and individually indicated to beincorporated by reference. Although the present invention has beendescribed in some detail by way of illustration and example for purposesof clarity and understanding, it will be apparent that certain changesand modifications may be practiced within the scope of the appendedclaims.

We claim:
 1. A method for enhanced transportation of materials,comprising: providing a device, comprising a plurality of fluidicchannels; adding a fluid containing an effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate NDSB into at least oneof said fluidic channels; controllably transporting at least a firstdiscrete fluid volume to a first location within said device, said firstdiscrete fluid volume comprising at least two differently chargedspecies wherein the 3-(N-ethyl-N,N-dimethylammonium)propanesulfonateNDSB reduces the electrophoretic mobility of the at least twodifferently charged species in the at least first discrete fluid volumerelative to an electroosmotic flow of said at least first discrete fluidvolume such that the first discrete fluid volume remains substantiallyunsmeared during transport to said first location.
 2. The method ofclaim 1, wherein the device comprises at least two intersecting fluidicchannels.
 3. The method of claim 1, wherein the controllablytransporting step comprises applying a voltage across the fluid channelto cause an electroosmotic flow of the at least first discrete fluidvolume.
 4. The method of claim 1, wherein the effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB) is within 1 mMto 2M.
 5. The method of claim 1, wherein the effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB) is within 5 mMto 2M.
 6. The method of claim 1, wherein the effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB) is greater than5 mM.
 7. The method of claim 1, wherein the effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB) is greater than10 mM.
 8. The method of claim 1, wherein the effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB) is geater than50 mM.
 9. The method of claim 1, wherein the at least two differentlycharged species may be selected from a group consisting of enzymes,ligands, and receptors.
 10. A device for enhanced material direction andtransport comprising: a plurality of fluidic channels, at least one ofsaid fluidic channels comprising at least a first discrete fluid volumeto be transported, said first discrete fluid volume comprising at leasttwo differently charged species; a power source connected to at least afirst one of said fluidic channels for applying a voltage gradientacross said first channel; and an effective concentration of3-N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB) contained withinsaid first discrete fluid volume whereby the electrophoretic mobility ofthe two differently charged species in the first discrete fluid volumerelative to an electroosmotic flow of said first discrete fluid volume,is reduced, such that the first discrete fluid volume remainssubstantially unsmeared during transport along said first channel. 11.The device of claim 10, comprising at least two intersecting fluidicchannels.
 12. The device of claim 10, wherein the material to betransported may be selected from a group consisting of enzymes, ligands,and receptors.
 13. The device of claim 10, wherein the effectiveconcentration of 3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB)is within 1 mM to 2M.
 14. The device of claim 10, wherein the effectiveconcentration of 3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB)is within 5 mM to 2M.
 15. The device of claim 10, wherein the effectiveconcentration of 3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB)is greater than 5 mM.
 16. The device of claim 10, wherein the effectiveconcentration of 3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB)is greater than 10 mM.
 17. The device of claim 10, wherein the effectiveconcentration of 3-(N-ethyl-N,N-dimethylammonium)propanesulfonate (NDSB)is greater than 50 mM.
 18. A method for enhanced transportation ofmaterials, comprising: providing a device, comprising a plurality offluidic channels; adding to at least one of said fluidic channels firstand second discrete fluid volumes and an effective concentration of3-(N-ethyl-N,N-dimethylammonium)propanesulfonate NDSB in at least one ofsaid first and second discrete fluid volumes; controllably transportingsaid first and second discrete fluid volumes to a first location withinsaid device, said first and second discrete volumes each comprising atleast two differently charged species wherein the3-(N-ethyl-N,N-dimethylammonium)propanesulfonate NDSB reduces theelectrophoretic mobility of the at least two differently charged speciesin the at least one of said first and second discrete fluid volumesrelative to an electroosmotic flow of said at least one first and seconddiscrete fluid volumes such that the first discrete fluid volume remainssubstantially unsmeared with the second discrete fluid volume duringtransport to said first location.